JP2015042274A - Electronic endoscope system, processor for electronic endoscope, and operation method of electronic endoscope system - Google Patents

Abstract

PROBLEM TO BE SOLVED: To accurately and surely track a target such as a lesion.SOLUTION: A wide-band light image 63, when the body cavity is irradiated by wide-band light BB, is obtained at intervals of a fixed time. In a tracking mode, a specific regional frame Ra is displayed in the wide-band light image 63. When a part such as a lesion enters in this specific regional frame Ra, a lock-on switch installed in an operation unit is pressed. In accordance with the pressing of the lock-on switch, a part in the specific regional frame is specified as a tracking target S, with blood vessel information of this tracking target S calculated. After the tracking target is specified, by moving an insertion part 16 or a tip end part 16a, a wide-band light image 64 is newly obtained which is different from the wide-band light image 63 at the time of the lock-on. In this newly obtained wide-band light image 64, an area Ra' is detected which includes the blood vessel information of the tracking target S. By repeating this detection, the tracking target S is tracked in a series of flow for obtaining the wide-band light image 64.

Description

  The present invention relates to an electronic endoscope system for tracking a tracking target such as a lesion in a body cavity, a processor device for the electronic endoscope, and a method for operating the electronic endoscope system.

  In the medical field in recent years, many diagnoses and treatments using an electronic endoscope have been performed. The electronic endoscope includes an elongated insertion portion that is inserted into the body cavity of a subject, and an imaging device such as a CCD is built in the distal end of the insertion portion. Further, the electronic endoscope is connected to the light source device, and the light emitted from the light source device is irradiated to the inside of the body cavity from the distal end of the insertion portion. In this manner, the subject tissue in the body cavity is imaged by the imaging device at the distal end of the insertion portion in a state where light is irradiated inside the body cavity. An image obtained by imaging is displayed on a monitor after various processing is performed by a processor device connected to the electronic endoscope.

  By using the electronic endoscope in this way, an image in the body cavity of the subject can be acquired in real time. From the captured image of the body cavity obtained in real time, not only the entire subject tissue but also each part of the subject tissue such as microvessel, deep blood vessel, pit pattern (gland opening structure), uneven structure such as depression or bulge is observed can do. At the time of diagnosis, it is determined whether or not there is a lesion such as a tumor site from the situation of the entire subject tissue or each site of the subject tissue.

  When a lesion is found from an image in the body cavity, the operator moves the endoscope tip up / down / left / right to check whether the found lesion has spread to other locations, By further inserting or pulling out from the inner side of the body cavity, an image of the periphery of the found lesion is taken. At this time, by moving the distal end portion of the endoscope up and down, left and right, the lesion site that was first discovered may be lost. In order to prevent this, as in Patent Document 1, a lesioned part is detected as a feature point from an image in the body cavity, and the detected feature point is tracked so that the lesioned part is not lost. it can.

JP 2002-95625 A

  In Patent Literature 1, when tracking feature points, it is considered that tracking is performed after a pattern such as a lesion is recognized. However, when tracking is performed based on pattern recognition, it may be difficult to accurately and reliably detect a portion similar to the recognized pattern from a newly acquired image. Accordingly, tracking of the tracking target based on pattern recognition may be inferior in terms of accuracy.

  According to the present invention, a tracking target such as a lesioned part can be accurately detected even if a doctor enlarges or distantly views an endoscopic image or moves an endoscope tip part up, down, left, or right depending on the diagnosis situation. It is another object of the present invention to provide an electronic endoscope system, a processor device for the electronic endoscope, and an operation method of the electronic endoscope system that can be reliably tracked.

  The electronic endoscope system of the present invention images a body light source that emits broadband light, a special light source that emits special light having a specific wavelength band that is different from the wavelength band of the broadband light, and the body cavity being illuminated with the broadband light An imaging signal acquisition means for acquiring a special imaging signal by imaging a body cavity being illuminated with special light, an image generation means for generating a broadband optical image from the broadband imaging signal, and broadband light. In a tracking target designating unit for designating a tracking target from an image, a biological information acquiring unit for acquiring biological information of the tracking target from a special imaging signal, and a broadband optical image generated after designating the tracking target, the biological information acquiring unit Tracking means for tracking the tracking target using the acquired biological information of the tracking target.

  A processor device for an electronic endoscope incorporated in the electronic endoscope system of the present invention includes a broadband light source that emits broadband light, and a special light source that emits special light having a specific wavelength band different from the wavelength band of the broadband light. An imaging signal acquisition means for imaging a body cavity under illumination with broadband light to acquire a broadband imaging signal, an imaging of a body cavity under illumination with special light to acquire a special imaging signal, and a tracking target designating means. In the processor apparatus, the receiving means for receiving the broadband imaging signal and the special imaging signal from the imaging signal acquisition means, the image generating means for generating a broadband optical image from the broadband imaging signal, and the tracking target specifying means from the special imaging signal Biometric information acquisition means for acquiring biological information of a tracking target designated from a broadband optical image by a broadband optical image generated after designation of the tracking target, Using the acquired biological information tracked in acquisition means and a tracking means for tracking the target object.

  The operation method of the electronic endoscope system according to the present invention includes a step in which a broadband light source emits broadband light, and an imaging signal acquisition means acquires a broadband imaging signal by imaging the inside of a body cavity illuminated with the broadband light. And a step of generating a broadband optical image from the broadband imaging signal, a step of specifying a tracking target from the broadband optical image, and a special light source having a wavelength band of the broadband light. Emitting special light having a specific wavelength band different from the step, the imaging signal acquisition means acquiring a special imaging signal by imaging the inside of a body cavity illuminated with special light, and the biological information acquisition means The step of acquiring biological information of the tracking target from the imaging signal and the tracking target raw information acquired by the biological information acquisition unit in the broadband optical image generated after the tracking unit specifies the tracking target. And a step of tracking a tracking object by using the information.

  The tracking target designating unit preferably includes a display unit that displays a designated area frame in the broadband light image, and a lock-on unit that designates a part in the designated area frame as a tracking target. The biometric information acquisition unit preferably includes a storage unit that stores biometric information to be tracked at the time designated by the lock-on unit. The biometric information acquisition means may acquire at least one of a blood vessel depth indicating a distance to a position where a blood vessel exists in the subject tissue, a blood concentration indicating a hemoglobin index, and an oxygen saturation as the biometric information. preferable.

  In an electronic endoscope system in which a special light source emits illumination light including at least three wavelength bands different from each other in a wavelength range of 400 nm to 600 nm and the wavelength band includes a blue band and a green band. The imaging signal acquisition means is a narrow band signal included in an imaging signal obtained by imaging a subject tissue including a blood vessel in a body cavity illuminated with illumination light as a special imaging signal, and has narrow wavelength bands different from each other. A plurality of narrowband signals respectively corresponding to the band light are obtained, and the biological information acquisition means obtains blood vessel information including blood vessel depth information relating to the blood vessel depth and blood concentration information relating to the blood concentration based on the plurality of narrowband signals. It is preferable to provide a first blood vessel information calculating means for obtaining.

  The imaging signal acquisition means includes first and second narrowband signals corresponding to the first and second narrowband lights in the blue band having different wavelength bands and a third narrowband corresponding to the third narrowband light in the green band. Preferably, the first blood vessel information calculating means obtains the blood vessel depth information and the blood concentration information based on the first to third narrow band signals. The first blood vessel information calculating means includes a luminance ratio calculating unit that calculates a first luminance ratio between the first and second narrowband signals and a second luminance ratio between the second and third narrowband signals; And referring to the correlation between the blood vessel depth-blood concentration correlation storage unit that stores in advance the correlation between the second luminance ratio and the blood vessel depth and blood concentration, and the correlation between the blood vessel depth-blood concentration correlation storage unit, It is preferable to include a blood vessel depth-blood concentration calculation unit for obtaining blood vessel depth information and blood concentration information corresponding to the first and second luminance ratios calculated by the luminance ratio calculation unit. The wavelength band of the first narrowband light is preferably 405 ± 10 nm, the wavelength band of the second narrowband light is 470 ± 10 nm, and the wavelength band of the third narrowband light is preferably 560 ± 10 nm.

  In an electronic endoscope system in which a special light source emits illumination light including a wavelength region having a central wavelength of 450 nm or less, the imaging signal acquisition means includes a subject including a blood vessel in a body cavity illuminated with illumination light as the special imaging signal A plurality of narrowband signals corresponding to a plurality of narrowband lights having different wavelength bands and at least one central wavelength of 450 nm or less, which are narrowband signals included in an imaging signal obtained by imaging a tissue The biological information acquisition means includes second blood vessel information calculation means for obtaining blood vessel information including blood vessel depth information related to blood vessel depth and oxygen saturation information related to oxygen saturation based on a plurality of narrowband signals. It is preferable. The multiple narrowband signals include wavelengths that exhibit different absorbances for reduced hemoglobin that is not bound to oxygenated oxygen bound to oxygen and that differ in absorbance for each hemoglobin due to oxygen saturation. Preferably it is.

  The imaging signal acquisition means has first and second narrowband signals corresponding to the first and second narrowband lights in the blue band having different wavelength bands, and a different wavelength band from the first and second narrowband lights. The fourth narrowband signal corresponding to the fourth narrowband light is acquired, and the second blood vessel information calculating means obtains the third luminance ratio between the first and fourth narrowband signals and the first and second narrowband signals. A luminance ratio calculation unit that calculates a fourth luminance ratio between them, and a blood vessel depth-oxygen saturation correlation storage unit that prestores correlations between the third and fourth luminance ratios, blood vessel depth, and oxygen saturation The blood vessel depth information and the oxygen saturation information corresponding to the third and fourth luminance ratios calculated by the luminance ratio calculation unit are obtained with reference to the correlation of the blood vessel depth-oxygen saturation correlation storage unit. It is preferable to include a blood vessel depth-oxygen saturation calculation unit. The wavelength band of the first narrowband light is preferably 405 ± 10 nm, the wavelength band of the second narrowband light is 470 ± 10 nm, and the wavelength band of the fourth narrowband light is preferably 440 ± 10 nm.

  According to the present invention, since tracking is performed using the biological information of the tracking target, the tracking can be performed even if the endoscope image is enlarged or distant, or the endoscope tip is moved up, down, left, or right. It is possible to accurately and reliably track the object.

It is an external view of the electronic endoscope system of the present invention. It is a block diagram which shows the electrical constitution of the electronic endoscope system of this invention. (A) is a CCD imaging operation in the normal observation mode or tracking target designation processing, (B) is a CCD imaging operation in the blood vessel information acquisition processing, and (C) is a CCD imaging operation in the tracking target detection processing. It is explanatory drawing explaining these. It is an image figure in the body cavity displayed on a monitor. It is explanatory drawing explaining the state of the insertion surface of the endoscope in a body cavity, and the state of the body cavity inner wall surface imaged in the insertion state, (B) was imaged further back | inner side from the insertion position of (A) Represents that. It is explanatory drawing explaining the state in the body cavity image | photographed in the insertion state of the endoscope in a body cavity, and the insertion state, (B) was imaged further back | inner side from the insertion position of (A) Represents. It is explanatory drawing explaining the state of the insertion surface of the endoscope in a body cavity, and the state of the body cavity inner wall surface imaged in the insertion state, (B) was imaged on the near side from the insertion position of (A) (C) shows that the image was taken on the back side from the insertion position of (B). It is a graph which shows correlation with 1st and 2 brightness | luminance ratio S1, S2, and blood vessel depth and blood concentration. It is a graph which shows the absorption coefficient of hemoglobin. It is a graph which shows correlation with 3rd and 4 brightness | luminance ratio S3, S4, blood vessel depth, and oxygen saturation. (A) shows the coordinates (S1 ^* , S2 ^* ) of the first and second luminance ratios in the luminance coordinate system, and (B) shows the coordinates (K ^* ) of the blood vessel information coordinate system corresponding to the coordinates (S1 ^* , S2 ^* ) ^. , L ^* ). (A) shows the coordinates (S3 ^* , S4 ^* ) of the third and fourth luminance ratios in the luminance coordinate system, and (B) shows the coordinates (U ^* ) of the blood vessel information coordinate system corresponding to the coordinates (S3 ^* , S4 ^* ) ^. , V ^* ). It is a flowchart which shows the effect | action of this invention. It is a block diagram which shows the electric constitution of the electronic endoscope system of embodiment different from this embodiment of this invention. It is the schematic of the rotation filter used with the electronic endoscope system of another embodiment.

  As shown in FIG. 1, an electronic endoscope system 10 according to the present invention includes an electronic endoscope 11 that images a body cavity of a subject, and an image of a subject tissue in the body cavity based on a signal obtained by the imaging. A processor device 12 for generating the light, a light source device 13 for supplying light for irradiating the inside of the body cavity, and a monitor 14 for displaying an image in the body cavity. The electronic endoscope 11 includes a flexible insertion portion 16 to be inserted into a body cavity, an operation portion 17 provided at a proximal end portion of the insertion portion 16, an operation portion 17, a processor device 12, and a light source device 13. And a universal cord 18 for connecting the two.

  A bending portion 19 in which a plurality of bending pieces are connected is formed at the distal end of the insertion portion 16. The bending portion 19 is bent in the vertical and horizontal directions by operating the angle knob 21 of the operation portion. The distal end of the bending portion 19 is provided with a distal end portion 16a incorporating an optical system for in-vivo imaging, and the distal end portion 16a is directed in a desired direction in the body cavity by the bending operation of the bending portion 19. .

  A connector 24 is attached to the universal cord 18 on the processor device 12 and the light source device 13 side. The connector 24 is a composite type connector including a communication connector and a light source connector, and the electronic endoscope 11 is detachably connected to the processor device 12 and the light source device 13 via the connector 24.

  As shown in FIG. 2, the light source device 13 includes a broadband light source 30, a shutter 31, a shutter driving unit 32, first to fourth narrowband light sources 33 to 35, 38, a coupler 36, and a light source switching unit 37. And. The broadband light source 30 is a xenon lamp, a white LED, a micro white light source, or the like, and generates broadband light BB having a wavelength ranging from a red region to a blue region (about 470 to 700 nm). The broadband light source 30 is always lit while the electronic endoscope 11 is in use. The broadband light BB emitted from the broadband light source 30 is collected by the condenser lens 39 and enters the broadband optical fiber 40.

  The shutter 31 is provided between the broadband light source 30 and the condenser lens 39. The shutter 31 is inserted in the optical path of the broadband light BB to block the broadband light BB, and the broadband light BB is retracted from the insertion position. It is movable between a retracted position that allows it to go to the condenser lens 39. The shutter drive unit 32 is connected to a controller 62 in the processor device, and controls the drive of the shutter 31 based on an instruction from the controller 62.

  The first to fourth narrowband light sources 33 to 35, 38 are laser diodes, LEDs, and the like, and the first narrowband light source 33 has a narrowband light in a blue band whose wavelength is limited to 400 ± 10 nm, preferably 405 nm. (Hereinafter referred to as “first narrowband light N1”), the second narrowband light source 34 has a narrowband light in a blue band whose wavelength is limited to 470 ± 10 nm, preferably 473 nm (hereinafter “second narrowband light”). The third narrow-band light source 35 is a narrow-band light in the green band whose wavelength is limited to 560 ± 10 nm, preferably 560 nm (hereinafter referred to as “third narrow-band light N3”). The fourth narrowband light source 38 generates narrowband light whose wavelength is limited to 440 ± 10 nm, preferably 445 nm (hereinafter referred to as “fourth narrowband light N4”). The first to fourth narrowband light sources 33 to 35 and 38 are connected to the first to fourth narrowband optical fibers 33a to 35a and 38a, respectively, and the first to fourth narrowband lights emitted from the respective light sources. N1 to N4 enter the first to fourth narrowband optical fibers 33a to 35a, 38.

  The coupler 36 connects the light guide 43 in the electronic endoscope to the broadband optical fiber 40 and the first to fourth narrowband optical fibers 33a to 35a, 38a. Thereby, the broadband light BB can be incident on the light guide 43 via the broadband optical fiber 40. Further, the first to fourth narrowband lights N1 to N4 can enter the light guide 43 via the first to fourth narrowband optical fibers 33a to 35a, 38a.

  The light source switching unit 37 is connected to a controller 62 in the processor device, and on the basis of an instruction from the controller 62, the first to fourth narrowband light sources 33 to 35, 38 are turned on (turned on) or turned off (off). Switch. In the normal observation mode, the broadband light BB is irradiated into the body cavity to capture a broadband optical image, while the first to fourth narrowband light sources 33 to 35, 38 are turned off. On the other hand, in the tracking mode for tracking a tracking target such as a lesion, there are three processes: a tracking target designating process, a blood vessel information acquisition process, and a tracking target detection process. Different.

  The tracking target designation process is a process until the tracking target is designated by lock-on, and in the same way as in the normal observation mode, the broadband light BB is irradiated into the body cavity and the broadband optical image is captured. The narrow band light sources 33 to 35, 38 are turned off. The blood vessel information acquisition process that is switched after the tracking target is locked on is a process of acquiring the blood vessel information of the tracking target. When switched to this blood vessel information acquisition process, the shutter 31 is set at the insertion position, The irradiation of the broadband light BB is stopped. When the irradiation of the broadband light BB is stopped, the first narrowband light source 33 is switched on by the light source switching unit 37. The subject tissue is imaged in a state where the first narrowband light N1 is irradiated into the body cavity. When the imaging is completed, a light source switching instruction is issued from the controller 62, and the first narrow band light source 33 is switched OFF and the second narrow band light source 34 is switched ON. When the imaging with the second narrowband light N2 applied to the body cavity is completed, the second narrowband light source 34 is switched off and the third narrowband light source 35 is switched on similarly. When the imaging with the third narrowband light N3 applied to the body cavity is completed, the third narrowband light source 35 is switched off and the fourth narrowband light source 38 is switched on. And when the imaging in the state which irradiated the 4th narrow-band light N4 in the body cavity is completed, the 4th narrow-band light source 38 will be switched OFF.

  The tracking target detection process switched after the blood vessel information acquisition process is a process for detecting a tracking target from the broadband optical image acquired after lock-on. When switched to the tracking target detection process, the shutter 31 is set at the retracted position. Is done. Then, after irradiating the body cavity with the broadband light BB for a certain period of time, the shutter 31 is set at the insertion position, and the irradiation of the broadband light BB into the body cavity is stopped. When the irradiation of the broadband light BB is stopped, similarly to the blood vessel information acquisition process, the first to fourth narrowband light sources 33 to 35 and 38 are sequentially switched on, and the first to fourth narrowband lights N1 to N4 are turned on. Is irradiated into the body cavity for a certain time. For each irradiation of the first to fourth narrowband lights N1 to N4, imaging is performed by the CCD 44 as in the blood vessel information acquisition process.

  The electronic endoscope 11 includes a light guide 43, a CCD 44, an analog processing circuit 45 (AFE: Analog Front End), and an imaging control unit 46. The light guide 43 is a large-diameter optical fiber, a bundle fiber, or the like. The incident end is inserted into the coupler 36 in the light source device, and the emission end is directed to the irradiation lens 48 provided at the distal end portion 16a. The light emitted from the light source device 13 is guided by the light guide 43 and then emitted toward the irradiation lens 48. The light incident on the irradiation lens 48 is irradiated into the body cavity through the illumination window 49 attached to the end surface of the distal end portion 16a. The broadband light BB and the first to fourth narrowband lights N1 to N4 reflected in the body cavity enter the condenser lens 51 through the observation window 50 attached to the end surface of the distal end portion 16a.

  The CCD 44 is a monochrome CCD, and receives light from the condenser lens 51 by the imaging surface 44a, photoelectrically converts the received light, and accumulates signal charges. Then, the accumulated signal charge is read as an imaging signal, and the read imaging signal is sent to the AFE 45. Here, the imaging signal when the broadband light BB is incident on the CCD 44 is referred to as a broadband imaging signal, and the imaging signals when the first to fourth narrowband lights N1 to N4 are incident on the CCD 44 are the first to fourth narrowband imaging signals. And

  The AFE 45 includes a correlated double sampling circuit (CDS), an automatic gain control circuit (AGC), and an analog / digital converter (A / D) (all not shown). The CDS performs correlated double sampling processing on the image pickup signal from the CCD 44 to remove noise generated by driving the CCD 44. The AGC amplifies the imaging signal from which noise has been removed by CDS. The A / D converts the imaging signal amplified by the AGC into a digital imaging signal having a predetermined number of bits and inputs the digital imaging signal to the processor device 12.

  The imaging control unit 46 is connected to the controller 62 in the processor device 12, and sends a drive signal to the CCD 44 when an instruction is given from the controller 62. The CCD 44 outputs an imaging signal to the AFE 45 at a predetermined frame rate based on the drive signal from the imaging control unit 46. When the normal observation mode is set, as shown in FIG. 3A, within the acquisition period of one frame, the step of photoelectrically converting the broadband light BB to accumulate the signal charge and the accumulated signal charge to the broadband A total of two operations are performed including a step of reading out as an imaging signal. This operation is repeated while the normal observation mode is set.

  In contrast, when the normal observation mode is switched to the tracking mode, the tracking target designation process is first set. In this tracking target designation process, a broadband imaging signal is read out by the same operation as in the normal observation mode in FIG. This operation is repeatedly performed while the tracking target specifying process is set.

  Next, when the tracking target designation process is switched to the blood vessel information acquisition process, as shown in FIG. 3B, the signal charge is accumulated by photoelectrically converting the first narrowband light N1 within the acquisition period of one frame. And a step of reading the accumulated signal charge as the first narrow-band imaging signal are performed in total. When the reading of the first narrowband imaging signal is completed, the step of photoelectrically converting the second narrowband light N2 to accumulate the signal charge within the acquisition period of one frame, and the accumulated signal charge to the second narrowband imaging signal Are read out.

  When the reading of the second narrowband imaging signal is completed, the step of photoelectrically converting the third narrowband light N3 and accumulating the signal charge within the acquisition period of one frame, and the accumulated signal charge as the third narrowband imaging signal Are read out. When the reading of the third narrowband imaging signal is completed, a step of photoelectrically converting the fourth narrowband light N4 and accumulating signal charges within the acquisition period of one frame, and the accumulated signal charges are converted into the fourth narrowband imaging signal. Are read out.

  Next, when the blood vessel information acquisition process is switched to the tracking target detection process, as shown in FIG. 3C, first, within the acquisition period of one frame, the same as the normal observation mode of FIG. By this operation, the broadband imaging signal is read out. When the readout of the wideband imaging signal is completed, the first to fourth narrowband imaging signals are read out by the same operation as the blood vessel information acquisition process in FIG. A series of operations of reading the broadband imaging signal → reading the first to fourth narrowband imaging signals is repeatedly performed while the tracking target detection process is set.

  As shown in FIG. 2, the processor device 12 includes a digital signal processor 55 (DSP (Digital Signal Processor)), a frame memory 56, an endoscope image generator 57, a display control circuit 58, and a tracking unit 60. The controller 62 controls each part. The DSP 55 performs wideband image data by performing color separation, color interpolation, white balance adjustment, gamma correction, and the like on the wideband imaging signal and the first to fourth narrowband imaging signals output from the AFE 45 of the electronic endoscope. And 1st-4th narrow-band image data are produced. The frame memory 56 stores the broadband image data and the first to fourth narrowband image data created by the DSP 55.

  The endoscopic image generation unit generates a broadband optical image 63 based on the broadband image data stored in the frame memory 56. The display control circuit 58 reads the broadband optical image 63 from the frame memory 56 and displays the read broadband optical image 63 on the monitor 14 as shown in FIG.

  The tracking unit 60 calculates the blood vessel information of the tracking target S based on the specified region frame setting unit 65 that sets the specified region frame Ra used for specifying the tracking target S and the first to fourth narrowband image data. The blood vessel information calculation unit 66, the lock-on information storage unit 67 for storing the blood vessel information calculated by the blood vessel information calculation unit 66, and the tracking target from the broadband light image 63 acquired after the tracking target S is specified based on the calculated blood vessel information And a tracking target detection unit 68 for detecting S.

  The designated area frame setting unit 65 sets the size of the designated area frame Ra and displays the designated area frame Ra on the monitor 14. Thereby, the tracking target S can be specified. Here, when designating the tracking target S, the surgeon first sets the angle knob 21 (see FIG. 4) so that the lesion to be tracked enters the designated area frame Ra as shown in FIG. 1). When a lesioned part or the like enters the designated area frame Ra, a lock-on switch 25 (see FIG. 1) provided on the operation unit 17 is pressed. As a result, a lesioned part or the like in the designated area frame Ra is designated as the tracking target S (lock-on).

  The blood vessel information calculation unit 66 obtains three blood vessel information of blood vessel depth, blood concentration, and oxygen saturation based on the first to fourth narrowband image data. The specific configuration of the blood vessel information calculation unit will be described later in detail. The lock-on information storage unit 67 stores the blood vessel information of the tracking target S calculated by the blood vessel information calculation unit 66.

  The tracking target detection unit 68 detects an area having the blood vessel information obtained by the blood vessel information calculation unit 66 or the blood vessel information stored in the lock-on information storage unit 67 from the broadband light image 64 acquired after the lock-on. Thus, by using the blood vessel information of the tracking target S obtained at the time of lock-on, the tracking target S can be tracked from the broadband optical image 64 obtained after the lock-on.

  For example, as shown in FIG. 5A, when a lesion on the wall of the body cavity is locked on as the tracking target S, the blood vessel information of the tracking target S that is locked on is “blood vessel depth: medium, When the blood concentration is high and the oxygen saturation is low, the blood vessel information is “blood vessel depth: medium, blood concentration: high, oxygen saturation: low” from the broadband optical image 64 obtained after lock-on. ”Is detected. Then, after the lock-on, when the surgeon further pushes the insertion portion 16 to the back side and a broadband optical image 64 as shown in FIG. 5B is obtained, from among the broadband optical image 64, An area Ra ′ in which the blood vessel information is “blood vessel depth: medium, blood concentration: high, oxygen saturation: low” is detected. Thereby, the tracking target S can be tracked.

  Further, as shown in FIG. 6A, when a small lesion is found on the back side in the body cavity, this lesion is locked on as the tracking target S, and blood vessel information of the tracking target S is obtained. . Then, as shown in FIG. 6B, the tracking target S is tracked from the obtained blood vessel information of the tracking target. Accordingly, the surgeon can push the insertion portion 16 or move the distal end portion 16a in the vertical and horizontal directions while grasping the tracking state of the tracking target S, so that the distal end portion 16a can be tracked easily and quickly. It can be made to approach the lesion part which is S.

  In addition, as shown in FIG. 7A, in the case where it is examined whether there is another lesion by metastasis or the like near the lesion found on the wall in the body cavity, the found lesion is tracked. Lock on as S. At the time of lock-on, the blood vessel information of the tracking target S is obtained and the obtained blood vessel information is stored in the lock-on information storage unit 67. Then, as shown in FIG. 7B, whether or not another lesion exists is checked by pushing or pulling out the insertion portion 16. And when confirming the lesion part discovered first, again, the insertion part 16 is moved so that the front-end | tip part 16a may return to the vicinity of the lesion part. Then, as shown in FIG. 7C, an area Ra ′ having blood vessel information stored in the lock-on information storage unit 67 is detected from the broadband light image 69. Thereby, even if the lesion part first discovered on the monitor 14 disappears, the lesion part can be confirmed again by the tracking function of the tracking target S of the present invention.

  As shown in FIG. 2, the blood vessel information calculation unit 66 includes a luminance ratio calculation unit 70, a blood vessel depth-blood concentration correlation storage unit 71, a blood vessel depth-oxygen saturation correlation storage unit 72, and a blood vessel depth. And a blood concentration calculator 73 and a blood vessel depth-oxygen saturation calculator 74. The luminance ratio calculation unit 70 specifies a blood vessel region including a blood vessel from the first to fourth narrowband light image data stored in the frame memory 56. As a method for specifying the blood vessel region, for example, there is a method for obtaining the blood vessel region from the difference between the luminance value of the blood vessel portion and the other luminance values.

  Then, the luminance ratio calculation unit 70 calculates the first luminance ratio S1 (Log (B1 / B1 / B1) between the first and second narrowband image data for the pixel at the same position in the blood vessel region and the same pixel position in the blood vessel region. B2)) and a second luminance ratio S2 (Log (G / B2)) between the third and second narrowband image data. Here, B1 is the brightness value of the pixel of the first narrowband light image data, B2 is the brightness value of the pixel of the second narrowband light image data, and G is the brightness value of the pixel of the third narrowband light image data. Represents. Further, a third luminance ratio S3 (B4 / B1) between the fourth and first narrowband image data is obtained, and a fourth luminance ratio S4 (B2 / B1) between the second and first narrowband image data is obtained. . Here, B4 represents the luminance value of the pixel of the fourth narrowband light image data.

  The blood vessel depth-blood concentration correlation storage unit 71 stores the correlation between the first and second luminance ratios S1 and S2, the blood concentration (hemoglobin index) in the blood vessel, and the blood vessel depth. This correlation is obtained by analyzing a large number of first to third narrowband optical image data accumulated in the diagnosis so far.

  As shown in FIG. 8, the blood vessel depth-blood concentration correlation storage unit 71 has coordinates of the luminance coordinate system 79 representing the first and second luminance ratios S1 and S2, and blood vessel information representing the blood concentration and the blood vessel depth. The correlation is stored by associating with the coordinates of the coordinate system 80. The blood vessel information coordinate system 80 is a KL coordinate system provided on the luminance coordinate system 79. The K axis represents the blood vessel depth and the L axis represents the blood concentration. The K axis has a positive slope because the blood vessel depth has a positive correlation with the luminance coordinate system 79. Regarding the K axis, the blood vessel is shallower as it goes diagonally to the left, and the blood vessel becomes deeper as it goes diagonally upward to the right. The L axis has a positive slope because the blood concentration has a positive correlation with the luminance coordinate system 79. With respect to the L axis, the blood concentration increases toward the lower left and the blood concentration decreases toward the upper right.

The blood vessel depth-oxygen saturation correlation storage unit 72 stores the correlation between the third and fourth luminance ratios S3 and S4 and the oxygen saturation in the blood vessel and the blood vessel depth. This correlation is a correlation when the blood vessel has the hemoglobin extinction coefficient shown in FIG. 9, and analyzes a large number of first, second, and fourth narrowband optical image data accumulated in the diagnosis so far. It is obtained by doing. As shown in FIG. 9, hemoglobin in a blood vessel has a light absorption characteristic in which the light absorption coefficient μa changes depending on the wavelength of light to be irradiated. The extinction coefficient μa represents an absorbance that is the magnitude of light absorption of hemoglobin, and is a coefficient of an expression of I ₀ exp (−μa × x) representing the attenuation state of light irradiated to hemoglobin. Here, I ₀ is the intensity of light emitted from the light source device to the subject tissue, and x (cm) is the depth to the blood vessel in the subject tissue.

  Further, the reduced hemoglobin 82 that is not bonded to oxygen and the oxidized hemoglobin 83 that is bonded to oxygen have different light absorption characteristics, and the isosbestic points (the respective hemoglobins 82, Except for the 83 intersection points), there is a difference in absorbance. If there is a difference in absorbance, the luminance value changes even if the same blood vessel is irradiated with light of the same intensity and the same wavelength. Further, even when light of the same intensity is irradiated, if the wavelength is different, the extinction coefficient μa changes, so that the luminance value changes.

  Considering the light absorption characteristics of hemoglobin as described above, there are 445 nm and 473 nm wavelengths that differ in absorbance depending on oxygen saturation, and a short wavelength region with a short depth of penetration is necessary for blood vessel depth information extraction. Therefore, it is preferable that the first, second, and fourth narrowband lights N1, N2, and N4 include at least one narrowband light having a wavelength region with a center wavelength of 450 nm or less. Moreover, even if the oxygen saturation is the same, the absorption coefficient value is different for different wavelengths, and the depth of penetration in the mucosa is also different. Therefore, the correlation between the brightness ratio and the blood vessel depth can be obtained by using the characteristics of light having a different depth of penetration depending on the wavelength.

  As shown in FIG. 10, the blood vessel depth-oxygen saturation correlation storage unit 72 represents the coordinates of the luminance coordinate system 85 representing the third and fourth luminance ratios S3 and S4, the oxygen saturation, and the blood vessel depth. Correlation is stored in association with the coordinates of the blood vessel information coordinate system 86. The blood vessel information coordinate system 86 is a UV coordinate system provided on the luminance coordinate system 85, the U axis represents the blood vessel depth, and the V axis represents the oxygen saturation. The U axis has a positive slope because the blood vessel depth has a positive correlation with the luminance coordinate system 85. Regarding the U-axis, the blood vessel is shallower as it goes diagonally upward to the right, and the blood vessel is deeper as it goes diagonally downward to the left. On the other hand, since the oxygen saturation has a negative correlation with the luminance coordinate system 85, the V-axis has a negative slope. With respect to this V-axis, the oxygen saturation is lower as it goes to the upper left, and the oxygen saturation is higher as it goes to the lower right.

  In the blood vessel information coordinate system 86, the U axis and the V axis are orthogonal to each other at an intersection point P. This is because the magnitude relationship of light absorption is reversed between when the first narrowband light N1 is irradiated and when the second narrowband light N2 is irradiated. That is, as shown in FIG. 9, when the fourth narrowband light N4 having a wavelength of 440 ± 10 nm is irradiated, the extinction coefficient of reduced hemoglobin 82 is higher than the extinction coefficient of oxyhemoglobin 83 having high oxygen saturation. In contrast, when the second narrowband light N2 having a wavelength of 470 ± 10 nm is irradiated, the extinction coefficient of oxyhemoglobin 83 is larger than the extinction coefficient of reduced hemoglobin 82. The magnitude relationship is reversed. Note that when the narrow band light whose light intensity magnitude relationship is not reversed is irradiated instead of the first, second, and fourth narrow band lights N1, N2, and N4, the U axis and the V axis are not orthogonal to each other. When the first narrowband light N1 having a wavelength of 400 ± 10 nm is irradiated, the extinction coefficients of oxyhemoglobin and reduced hemoglobin are substantially equal.

As shown in FIG. 11A, the blood vessel depth-blood concentration calculating unit 73 uses coordinates (S1 ^*) corresponding to the first and second luminance ratios S1 ^* and S2 ^* as observed values in the luminance coordinate system 79 ^. , S2 ^* ). When the coordinates (S1 ^* , S2 ^* ) are specified, the coordinates (K ^* , L ^* ) corresponding to the coordinates (S1 ^* , S2 ^* ) in the blood vessel information coordinate system 80 as shown in FIG. Identify. Thereby, the blood vessel depth information K ^* and the blood concentration information L ^* are obtained for the pixel at a predetermined position in the blood vessel region.

As shown in FIG. 12A, the blood vessel depth-oxygen saturation calculation unit 74 has coordinates (S3) corresponding to the third and fourth luminance ratios S3 ^* and S4 ^* as observed values in the luminance coordinate system 85. ^* , S4 ^* ). When the coordinates (S3 ^* , S4 ^* ) are specified, coordinates (U ^* , V ^* ) corresponding to the coordinates (S3 ^* , S4 ^* ) in the blood vessel information coordinate system 86 as shown in FIG. Identify. Thereby, blood vessel depth information U ^* and oxygen saturation information V ^* are obtained for a pixel at a predetermined position in the blood vessel region.

  Next, the effect | action of this invention is demonstrated along the flowchart shown in FIG. First, the normal observation mode is switched to the tracking mode by operating the console 23. When the tracking mode is switched, the designated area frame Ra is displayed on the monitor 14. Then, until the tracking target S is locked on (designation of the tracking target S), the process proceeds to a tracking target designation process in which the broadband light BB is irradiated into the body cavity. In this tracking target designation process, the surgeon further pushes the insertion portion 16 so that the tracking target S such as a lesioned portion falls within the designated area frame Ra, or operates the angle knob 21 or the like of the operation portion to move the distal end portion. 16a is moved vertically and horizontally. When the tracking target S enters the designated area frame Ra, the operator presses the lock-on switch 25.

  When the lock-on switch 25 is pressed, the process proceeds to blood vessel information acquisition processing for obtaining blood vessel information of the tracking target S. In the blood vessel information acquisition process, first, the shutter drive unit 32 stops the irradiation of the broadband light BB into the body cavity by setting the shutter 31 at the insertion position. Then, the first to fourth narrowband light sources 33 to 35 and 38 are sequentially turned on at regular intervals, and the first to fourth narrowband lights N1 to N4 are irradiated into the body cavity at regular intervals. The first to fourth narrowband imaging signals are acquired by performing imaging for each irradiation of the first to fourth narrowband lights N1 to N4. The first to fourth narrowband imaging signals obtained by imaging are sent to the DSP 55 via the AFE 45. The DSP 55 generates first to fourth narrowband image data based on the first to fourth narrowband imaging signals. The generated first to fourth narrowband image data is stored in the frame memory 56.

  The blood vessel information calculation unit 66 calculates the blood vessel information of the tracking target S based on the first to fourth narrowband image data stored in the frame memory 56. Three pieces of blood vessel information are required: blood vessel depth, blood concentration, and oxygen saturation. The calculated blood vessel information of the tracking target S is stored in the lock-on information storage unit 67. When the blood vessel information is stored in the lock-on information storage unit 67, the blood vessel information acquisition process ends, and the process automatically proceeds to the tracking target detection process.

  In the tracking target detection process, a series of irradiation of broadband light BB → irradiation of first narrowband light N1 → irradiation of second narrowband light N2 → irradiation of third narrowband light N3 → irradiation of fourth narrowband light N4 The shutter 31 and the first to fourth narrowband light sources 33 to 35 and 38 are driven and controlled so that the operation is repeated. Thereby, after the lock-on, the broadband image data and the first to fourth narrowband image data are obtained at regular time intervals. The monitor 14 displays a broadband optical image 63 based on the obtained broadband image data.

  In addition, the blood vessel information calculation unit 66 calculates blood vessel information in the body cavity for the broadband optical image 64 obtained after lock-on based on the obtained first to fourth narrowband image data. The tracking target detection unit 68 detects whether or not there is an area Ra ′ having blood vessel information stored in the lock-on information storage unit 67 from the broadband light image 64. If it exists, the designated area frame Ra is displayed in accordance with the area Ra ′ to notify the surgeon that the part in the area Ra ′ is the tracking target S designated by lock-on. Thereby, the tracking target S can be tracked. Then, until the tracking mode is switched to the normal observation mode, the tracking target S is continuously tracked by repeating the same processing as before. Then, when the tracking mode is switched to the normal observation mode, the tracking of the tracking target S ends.

  On the other hand, if the area Ra ′ having blood vessel information stored in the lock-on information storage unit 67 does not exist in the broadband light image 64, the same processing as before is performed until the tracking target S is detected. Repeated.

  In this embodiment, in addition to the broadband light source, the first to fourth narrowband light sources are used to irradiate the broadband light BB and the first to fourth narrowband light, but instead of this, FIG. As shown in FIG. 4, the broadband light BB and the first to the first light beams using the broadband light source 30 and the rotary filter 100 including a filter that transmits light used in the normal observation mode and the tracking mode among the broadband light BB from the broadband light source. You may perform irradiation of 4th narrow-band light. The rotary filter 100 is provided between the broadband light source 30 and the condenser lens 39, and rotates at a constant speed around the rotation axis 100a. The rotary filter 100 is movable in the radial direction by a filter switching unit 101 attached to the rotary shaft 100a.

  As shown in FIG. 15, the rotary filter 100 includes a first area 102 that transmits light used during tracking target designation processing in the normal observation mode and the tracking mode among the broadband light BB from the broadband light source 30, and the broadband light BB. Among them, a second area 103 that transmits light used during blood vessel information acquisition processing and a third area 104 that transmits light used during tracking target detection processing among the broadband light BB are provided. Therefore, when switching modes and processes, the filter switching unit 101 moves the rotary filter 100 in the radial direction so that the area corresponding to the mode or process to be switched is positioned on the optical path of the broadband light BB. .

  The first area 102 is provided with a broadband light transmission filter 105 that transmits the broadband light BB as it is. In the second area 103, the first narrowband light transmission filter 106 that transmits only the first narrowband light N1 out of the broadband light BB, and the second narrowband light transmission filter 107 that transmits only the second narrowband light. And a third narrowband light transmission filter 108 that transmits only the third narrowband light, and a fourth narrowband light transmission filter 109 that transmits only the fourth narrowband light in this order along the circumferential direction. It has been. In the third area, a broadband light transmission filter 105 and first to fourth narrowband light transmission filters 106 to 109 are provided in this order along the circumferential direction.

  In the present embodiment, the case where there is one tracking target has been described, but a plurality of tracking targets may exist. When there are a plurality of tracking targets, it is necessary to obtain blood vessel information for each tracking target and store each blood vessel information as in the case where the tracking target is 1. In the present embodiment, the tracking target is tracked using three of the blood vessel depth, the blood concentration, and the oxygen saturation, but the tracking may be performed only with at least one of them.

  In this embodiment, tracking is performed using the blood vessel information to be tracked. In addition to the blood vessel information to be tracked, tracking is performed using biological information such as a pit pattern, a blood vessel shape, and a blood vessel thickness. Also good. Moreover, it is good also considering the site | part which has autofluorescence components, such as collagen, NADH, and FAD among the object tissues | organisms in a body cavity as a tracking object. In this case, excitation light (for example, 405 nm narrow-band light) is irradiated to the tracking target serving as an autofluorescence component to generate autofluorescence, and fluorescence information such as the light intensity of the generated autofluorescence is used. Follow up. Furthermore, when a tumor-affinity photosensitive substance (fluorescent drug) such as a porphyrin derivative is administered to a patient, a tumor affected part in which the fluorescent drug has accumulated may be set as a tracking target. In this case, excitation light (for example, 405 nm narrow-band light) is irradiated to the tumor affected part where the fluorescent drug is accumulated to generate fluorescence, and tracking is performed using fluorescence information such as the light intensity of the generated fluorescence. Do.

  In the present embodiment, during tracking target detection processing, blood vessel information in the body cavity is obtained from the entire broadband optical image acquired after lock-on. If the movement of the tracking target can be predicted to some extent, the prediction is expected. Blood vessel information may be obtained only within the range of movement of the tracking target. Further, in this embodiment, when the tracking mode is switched, the designated area frame is displayed on the monitor, and the part within the designated area is designated as the tracking target. Instead, the tracking area is switched to the tracking mode. At the time, the designated area frame is not displayed on the monitor, but when a lesion or the like is designated with a pointer displayed on the monitor using a mouse or a console, the designated area frame is placed around the designated lesion area. You may make it display.

  The present invention can be applied not only to an insertion type electronic endoscope having an insertion portion or the like, but also to a capsule type electronic endoscope in which an imaging element such as a CCD is incorporated in a capsule.

DESCRIPTION OF SYMBOLS 10 Electronic endoscope system 30 Broadband light source 33-35,38 1st-4th narrowband light source 44 CCD
57 Endoscopic image generation unit 60 Tracking unit 63 Broadband light image 65 Designated region frame setting unit 66 Blood vessel information calculation unit 67 Lock-on information storage unit 68 Tracking target detection unit 70 Luminance ratio calculation unit 71 Blood vessel depth-blood concentration correlation Storage unit 72 Blood vessel depth-blood concentration calculation unit 73 Blood vessel depth image generation unit 74 Blood concentration image generation unit Ra Specified area frame S Tracking target

Claims (14)

A broadband light source that emits broadband light;
A special light source that emits special light having a specific wavelength band different from the wavelength band of the broadband light;
Imaging signal acquisition means for acquiring a broadband imaging signal by imaging the inside of a body cavity illuminated with the broadband light, and acquiring a special imaging signal by imaging the interior of the body cavity illuminated with the special light;
Image generating means for generating a broadband optical image from the broadband imaging signal;
Tracking target designating means for designating a tracking target from the broadband optical image;
Biological information acquisition means for acquiring biological information of the tracking target from the special imaging signal;
A tracking unit that tracks the tracking target using the biological information of the tracking target acquired by the biological information acquisition unit in the broadband optical image generated after the tracking target is specified. Endoscopic system. The tracking target specifying means includes
Display means for displaying a designated area frame in the broadband optical image;
The electronic endoscope system according to claim 1, further comprising lock-on means for designating a part in the designated area frame as the tracking target.   The electronic endoscope system according to claim 2, wherein the biological information acquisition unit includes a storage unit that stores the biological information of the tracking target at a time specified by the lock-on unit.   The biological information acquisition means acquires at least one of a blood vessel depth indicating a distance to a position where a blood vessel exists in a subject tissue, a blood concentration indicating a hemoglobin index, and an oxygen saturation as the biological information. The electronic endoscope system according to any one of claims 1 to 3, wherein the electronic endoscope system is provided. 5. The special light source emits illumination light including at least three wavelength bands different from each other in a wavelength range of 400 nm to 600 nm, wherein the wavelength band includes a blue band and a green band. In electronic endoscope system,
The imaging signal acquisition means is a narrowband signal included in an imaging signal obtained by imaging a subject tissue including a blood vessel in the body cavity illuminated with the illumination light as the special imaging signal, and has different wavelengths. Obtain multiple narrowband signals, each corresponding to narrowband light with bandwidth,
The biological information acquisition means includes first blood vessel information calculation means for obtaining blood vessel information including blood vessel depth information relating to the blood vessel depth and blood concentration information relating to the blood concentration based on the plurality of narrowband signals. A featured electronic endoscope system. The imaging signal acquisition means includes first and second narrowband signals corresponding to the first and second narrowband lights in the blue band having different wavelength bands, and a third corresponding to the third narrowband light in the green band. Get narrowband signal and
6. The electronic endoscope system according to claim 5, wherein the first blood vessel information calculating means obtains the blood vessel depth information and the blood concentration information based on the first to third narrowband signals. The first blood vessel information calculating means includes
A luminance ratio calculator that calculates a first luminance ratio between the first and second narrowband signals and a second luminance ratio between the second and third narrowband signals;
A blood vessel depth-blood concentration correlation storage unit that stores in advance the correlation between the first and second luminance ratios, the blood vessel depth, and the blood concentration;
The blood vessel depth information and the blood concentration information corresponding to the first and second luminance ratios calculated by the luminance ratio calculation unit are obtained with reference to the correlation in the blood vessel depth-blood concentration correlation storage unit. The electronic endoscope system according to claim 6, further comprising a blood vessel depth-blood concentration calculation unit.   The wavelength band of the first narrowband light is 405 ± 10 nm, the wavelength band of the second narrowband light is 470 ± 10 nm, and the wavelength band of the third narrowband light is 560 ± 10 nm. The electronic endoscope system according to claim 6 or 7. The electronic endoscope system according to claim 4, wherein the special light source emits illumination light including a wavelength region having a center wavelength of 450 nm or less.
The imaging signal acquisition means is a narrowband signal included in an imaging signal obtained by imaging a subject tissue including a blood vessel in the body cavity illuminated with the illumination light as the special imaging signal, and has different wavelengths. Obtaining a plurality of narrowband signals respectively corresponding to a plurality of narrowband lights having a band and at least one central wavelength of 450 nm or less;
The biological information acquisition means includes second blood vessel information calculation means for obtaining blood vessel information including blood vessel depth information related to the blood vessel depth and oxygen saturation information related to the oxygen saturation based on the plurality of narrowband signals. An electronic endoscope system characterized by that.   The plurality of narrowband signals include wavelengths that exhibit different absorbances for reduced hemoglobin that is not bound to oxygenated hemoglobin that is bound to oxygen and that cause a difference in absorbance for each hemoglobin depending on oxygen saturation. The electronic endoscope system according to claim 9, wherein The imaging signal acquisition means includes first and second narrowband signals corresponding to first and second narrowband lights in blue bands having different wavelength bands, and different wavelength bands from the first and second narrowband lights. A fourth narrowband signal corresponding to the fourth narrowband light having
The second blood vessel information calculating means includes
A luminance ratio calculator that calculates a third luminance ratio between the first and fourth narrowband signals and a fourth luminance ratio between the first and second narrowband signals;
A blood vessel depth-oxygen saturation correlation storage unit that stores in advance the correlation between the third and fourth luminance ratios, the blood vessel depth, and the oxygen saturation;
The blood vessel depth information and the oxygen saturation information corresponding to the third and fourth luminance ratios calculated by the luminance ratio calculation unit with reference to the correlation of the blood vessel depth-oxygen saturation degree correlation storage unit The electronic endoscope system according to claim 9, further comprising: a blood vessel depth-oxygen saturation calculating unit that calculates   The wavelength band of the first narrowband light is 405 ± 10 nm, the wavelength band of the second narrowband light is 470 ± 10 nm, and the wavelength band of the fourth narrowband light is 440 ± 10 nm. The electronic endoscope system according to claim 11. A broadband light source that emits broadband light, a special light source that emits special light having a specific wavelength band different from the wavelength band of the broadband light, and a broadband imaging signal obtained by imaging the interior of a body cavity illuminated with the broadband light A processor device for an electronic endoscope incorporated in an electronic endoscope system, comprising: an imaging signal acquisition unit that acquires an image of the body cavity being illuminated with the special light to acquire a special imaging signal; and a tracking target designation unit In
Receiving means for receiving a broadband imaging signal and the special imaging signal from the imaging signal acquisition means;
Image generating means for generating the broadband optical image from the broadband imaging signal;
Biological information acquisition means for acquiring biological information of the tracking target specified from the broadband optical image by the tracking target specifying means from the special imaging signal;
A tracking unit that tracks the tracking target using the biological information of the tracking target acquired by the biological information acquisition unit in the broadband optical image generated after the tracking target is specified. A processor unit for an endoscope. A broadband light source emitting broadband light;
An imaging signal acquisition means for acquiring a broadband imaging signal by imaging the inside of a body cavity illuminated with the broadband light; and
An image generating means generating a broadband optical image from the broadband imaging signal;
A tracking target designating unit designating a tracking target from the broadband optical image;
A special light source emitting special light having a specific wavelength band different from the wavelength band of the broadband light; and
The imaging signal acquisition means acquires the special imaging signal by imaging the inside of the body cavity illuminated with the special light;
A biological information acquisition means acquires the biological information of the tracking target from the special imaging signal;
The tracking means comprises the step of tracking the tracking object using the biological information of the tracking object acquired by the biological information acquisition means in the broadband optical image generated after designating the tracking object. Method of operating an electronic endoscope system.

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